Coated Vaso-Occlusive Device for Treatment of Aneurysms

ABSTRACT

A method is described herein for the treatment of intracranial aneurysms. The method comprises inserting into an aneurysm an embolism coil coated with a polymeric coating comprising a genipin, such as genipin or a derivative thereof, thereby increasing the stability of clots within the aneurysm. According to one example, the coating is a poly(L-lactide-co-glycolide) (PLGA) is used to release genipin to crosslink fibrin clots thereby creating more stable occlusions. Increased clotting can improve segregation of the weakened portion of the blood vessel from the rest of the vasculature and reduce the risk of recurrence.

CROSS REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of U.S. Provisional PatentApplication No. 61/851,677, Filed Mar. 12, 2013, which is incorporatedherein by reference in its entirety.

BACKGROUND

Intracranial cerebral aneurysms are most commonly found as arterialsaccular dilatations located at points where parent arteries bifurcateinto branch vessels. The incidence of these lesions in human autopsystudies is approximately 5%. Most aneurysms remain asymptomatic due to alow rupture rate of 0.5 to 4% per year depending upon their size, shape,and location (average rate of rupture 1%). The mortaility rate afterrupture is between 30 and 60% if no treatment is administered. Of theremaining patients, outcome depends upon (1) the patient's neurologiccondition when he/she presents for care and (2) the complexity ofaneurysm treatment.

Current treatment for both ruptured and unruptured aneurysms includessurgical clipping (exovascular therapy) and catheter based intervention(endovascular therapy). The latter includes the placement of platinumcoils or liquid gels into the aneurysm to arrest blood flow within theaneurysm sac and induce thrombosis of the lesion and its subsequentexclusion from the native circulation and/or placement of stent likedevices across the aneurysm neck to achieve similar results. Someaneurysms are more amenable to one therapy or the other. Randomizedcontrolled studies have shown that when aneurysms are judged to be goodcandidates for either therapy, endovascular therapy leads to betterneurologic outcomes.

The primary downsides to endovascular aneurysm therapy are the risk ofaneurysm recurrence and subsequent lesion rupture or re-rupture. Whilerecurrence is possible when any aneurysm is treated endovascularly, theincreased likelihood of such an event is directly proportional toincreased aneurysm size, increase volume of pre-therapy intra-aneurysmalthrombus, and low fundus to neck ratio (fundal diameter primarily in thenon-Z plane divided by the aneurysm neck diameter). These differentcriteria affect the surgeon's ability to densely fill the aneurysm withcoil material so that coil compaction into the aneurysm's dome islimited. Such compaction is caused by a combination of arterial bloodpressure pulsations which force the coil loops to densely collapse onone another thus opening up new space in the aneurysm dome and byintra-aneurysmal thrombolysis which reduces the ability for thrombuswithin the aneurysm to organize and support the coil mass againstcollapse into the aneurysm dome.

In an attempt to reduce the incidence of aneurysm recurrence followingendovascular coiling, manufacturers have made several attempts to modifythe platinum coil surface, coil shape/geometry, and coil stiffness.These modifications all seek to induce the holy grail of endovascularaneurysm therapy, maximization of coil pack density within the aneurysm(close to or greater than 35% of total aneurysm volume filled with coilmaterial) and subsequent exclusion of the aneurysm neck from the nativecirculation and parent vessels by the induction of an endothelial layerthat covers the interface between the coil material in the aneurysm neckand the parent vessel lumen and arterial blood flow. It is the growth ofthis endothelial layer that seals the aneurysm off from the normalarterial blood flow thus eliminating the risk of aneurysm recurrence.

While all coil manufacturers have altered their product's geometry andstiffness in an attempt to maximize coil density within the aneurysmfundus, only two manufacturers have altered their coil surfaces andstudied the consequences of such alterations on aneurysm recurrence andendothelialization. Reinges et al. (Bare, Bio-Active and Hydrogel-CoatedCoils for Endovascular Treatment of Experimentally Induced Aneurysms:Long-Term Histological and Scanning Electron Microscopy Results.Interventional Radiology, 2010. 16(2): p. 139-150) studied the differentoutcomes after coiling of experimental aneurysm using, unmodifiedplatinum coils, hydrogel coated coils (HydroCoil, MicroventionTherapeutics), and bioactive coils coated with PLGA copolymers (MatrixCoil, Boston Scientific, Fremont, Calif.). The premise behind hydrogelcoating is that once the coil is inserted into the aneurysm the hydrogelswells, thus increasing the density of material within the aneurysmfundus and increasing the surface area of material at the neck of theaneurysm. These two effects of the coating presumably facilitateimproved endothelial growth across the aneurysm neck and subsequentaneurysm exclusion from the native circulation. The premise behind thePLGA coating of bioactive coils is for the PLGA to produce aninflammatory reaction within the aneurysm and at the neck of theaneurysm thus enhancing clot organization and maturation andaccelerating neointimal proliferation. The authors found that PLGAprovided no benefits compared to bare platinum coils. Hydrogel coilsincreased the likelihood of intraneurysmal fibrosis along with instancesof neoendothelial proliferation and endothelial spanning of tissue fromone coil loop to another leading to neck coverage. Murayama et al. (Ionimplantation and protein coating of detachable coils for endovasculartreatment of cerebral aneurysms: concepts and preliminary results inswine models. Neurosurgery, 1997. 40(6): p. 1233-43; discussion 1243-4)also looked to alter platinum coils using ion implantation and proteincoating with fibronectin. They found greater fibrous coverage of theaneurysm necks in the modified coils group compared to the bare platinumtreated animals. These experimental results have been partiallyconfirmed by clinical studies. Piotin et al. (Intracranial AneurysmsCoiling With Matrix: Immediate Results in 152 Patients and MidtermAnatomic Follow-Up From 115 Patients. Stroke, 2009. 40(1): p. 321-323)found that Matrix coils provided no improvement in aneurysmrecanalization rates compared to bare platinum coils.

Once an aneurysm is filled with coils, the influx of pulsating blood isreduced as hemodynamic pressure is distributed and absorbed by the coilmass. Intraneurysmal blood flow becomes turbulent and the process ofcoagulation can begin (Piotin, M., et al., Intracranial AneurysmsCoiling with Matrix: Immediate Results in 152 Patients and MidtermAnatomic Follow-Up From 115 Patients. Stroke, 2009. 40(1): p. 321-323).Histologic studies have shown that following coil placement in ananeurysm dome, platelets and fibrin deposit on the coil's loops. Overtime the fibrin clot organizes and granulation tissue forms between thecoil loops thus stabilizing them. This tissue forms a matrix over whichneoendothelial cells, which emerge from the surrounding healthy vesselwall, can gradually grow from the periphery to eventually cover theportion of the coils exposed to the arterial blood flow in the parentvessel's lumen. In the ideal situation, this neoendothelial layereffectively isolates the aneurysm from the arterial blood floweliminating the risk of subsequent aneurysm recanalization, recurrence,and rupture. However, the rate at which a complete neoendothelial layerforms is currently unknown. Literature suggests that after 5 days ofcoil deposition a thrombus consisting of erythrocytes and fibrin arefound throughout the dome. Within 2 weeks foamy macrophages are foundnear the coils and by 270 days scar formation with vascularizedconnective tissue surrounds the coils and fills the fundus whileendothelial cells seal the aneurysm neck. It is the surgeon's hope thatthis process can occur as quickly and reliably as possible since anideal outcome is contingent upon the completion of this process.

Histologic findings following the use of hydrogel coated coils suggestthat this material might enhance neoendothelial sealing of the aneurysmby promoting thrombosis through a more dense aneurysm fill and bypresenting a greater surface are at the neck over which neoendothelialcells can sprout and spread to form a contiguous membrane. While the useof hydrogel coatings may seem attractive, a subset of patients whounderwent HydroCoil implantation have developed delayed asepticmeningitis, intraparenchymal cyst formation, and hydrocephalus. It isunclear whether or not higher rates of aneurysm occlusion justify suchpotential complications.

SUMMARY

The methods and devices described herein are useful in the treatment ofaneurysms. A vaso-occlusive device, such as an embolism coil is providedcomprising a coating that incorporates, e.g., by mixing, genipin or acrosslinking genipin derivative, inclusive of pharmaceuticallyacceptable salts thereof, with the polymer during coating of the coil,or by absorption and/or adsorption of the genipin to the polymer.Genipins act as cross-linking agents, thereby increasing stability ofclots within the aneurysm by cross-linking fibrin and/or othercompositions comprising primary amines. According to one non-limitingembodiment, the polymeric coating is a bioerodible polymer such aspoly(L-lactide-co-glycolide) (PLGA), comprising genipin. Dissolution ofthe polymeric coating and/or elution of incorporated genipin results inrelease of genipin over time to crosslink fibrin clots, thereby creatinga more stable occlusion. Furthermore, this solution permits acceleratedhealing and remodeling of the vasculature and therefore is likely tosolve many of the problems with current treatments based on endovascularcoiling. Genipin is a naturally occurring compound that iscost-effective, easy to handle, and has been used in other food andmedical products. Taken together, the described methods and devices havethe possibility for revolutionizing endovascular coiling treatment ofintracranial aneurysms.

Accordingly in one embodiment of the methods provided herein, a methodof treating an aneurysm in a patient is provided. The method comprisesfeeding (that is, introducing, placing, etc.) a vaso-occlusive deviceand genipin or a crosslinking genipin derivative into a fundus of theaneurysm using a catheter. In one embodiment, the genipin or acrosslinking genipin derivative is incorporated into a bioerodiblepolymer. In another embodiment, the vaso-occlusive device, such as anembolism coil, comprises a core substrate and a controlled releasecoating layer on the core substrate comprising the genipin or acrosslinking genipin derivative. In one embodiment, the controlledrelease coating layer comprises genipin or a pharmaceutically acceptablesalt thereof. In another embodiment, the controlled release coatinglayer comprises a crosslinking derivative of genipin or apharmaceutically acceptable salt thereof. In one particular embodiment,crosslinking derivative of genipin is a compound according to formula 2or a stereoisomer or pharmaceutically acceptable salt thereof:

where R1 is —H, ═O or —OR4, where R4 is —H, C₁₋₆ alkyl, C₁₋₃ alkyl, orC₁₋₁₂ alkanoyl which can be substituted with phenyl, phenoxy, pyridyl orthienyl; R2 is H, C₁₋₆ alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl,isopropyl, butyl, n-butyl, t-butyl, isobutyl, or sec-butyl; and R3 is aprimary alcohol chosen from —CH₂—OH and —R5-CH₂—OH, where —R5- is C₁₋₆alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl, isopropyl, butyl, n-butyl,t-butyl, isobutyl, or sec-butyl, other than genipin. In one embodiment,R1 is —OR4, where R4 is —H or C₁₋₃ alkyl. In another embodiment, R2 is Hor C₁₋₃ alkyl and/or R3 is —CH₂—OH, —CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH. Inyet another embodiment, R2 is H or C₁₋₃ alkyl. In another embodiment, R3is —CH₂—OH, —CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH. In a further embodiment,the device comprises between the core substrate and the controlledrelease coating layer a polymeric intermediary layer, which isoptionally a hydrogel. According to one embodiment, the controlledrelease coating layer is a bioerodible polymer comprising the genipin orcrosslinking genipin derivative. Non-limiting examples of a bioerodiblepolymer are: a polyester, a polyester-containing copolymer, apolyanhydride, a polyanhydride-containing copolymer, a polyorthoester,and a polyorthoester-containing copolymer. In one embodiment, thepolyester or polyester-containing copolymer is apoly(lactic-co-glycolic) acid (PLGA) copolymer. In another embodiment,the bioerodible polymer is selected from the group consisting ofpoly(lactic acid) (PLA); poly(trimethylene carbonate) (PTMC);poly(caprolactone) (PCL); poly(glycolic acid) (PGA);poly(glycolide-co-trimethylenecarbonate) (PGTMC);poly(L-lactide-co-glycolide) (PLGA); polyethylene-glycol (PEG-)containing block copolymers; and polyphosphazenes. In one embodiment,the controlled release coating layer is a non-bioerodible polymercomprising the genipin or crosslinking genipin derivative.

In another embodiment, a vaso-occluding catheter device is provided. Thevaso-occluding catheter device comprises a sheath and a filament withinthe sheet, the filament comprising a core substrate and a controlledrelease coating layer on the core substrate comprising genipin or acrosslinking genipin derivative. In one embodiment, the core substrateis a metal, non-limiting examples of which include platinum, a platinumalloy or nitinol. In one embodiment, the controlled release coatinglayer comprises genipin or a pharmaceutically acceptable salt thereof.In another embodiment, the controlled release coating layer comprises acrosslinking derivative of genipin or a pharmaceutically acceptable saltthereof. Examples of the crosslinking genipin derivative include,without limitation, is a compound according to formula 2 or astereoisomer or pharmaceutically acceptable salt thereof:

where R1 is —H, ═O or —OR4, where R4 is —H, C₁₋₆ alkyl, C₁₋₃ alkyl, orC₁₋₁₂ alkanoyl which can be substituted with phenyl, phenoxy, pyridyl orthienyl; R2 is H, C₁₋₆ alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl,isopropyl, butyl, n-butyl, t-butyl, isobutyl, or sec-butyl; and R3 is aprimary alcohol chosen from —CH₂—OH and —R5-CH₂—OH, where —R5- is C₁₋₆alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl, isopropyl, butyl, n-butyl,t-butyl, isobutyl, or sec-butyl, other than genipin. In one example, R1is —OR4, where R4 is —H or C₁₋₃ alkyl. In another example, R2 is H orC₁₋₃ alkyl and/or R3 is —CH₂—OH, —CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH. In yetanother example, R2 is H or C₁₋₃ alkyl. In yet another example, R3 is—CH₂—OH, —CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH. The device optionallycomprises between the core substrate and the controlled release coatinglayer a polymeric intermediary layer, such as a hydrogel. In oneembodiment, the controlled release coating layer is a bioerodiblepolymer comprising the genipin or crosslinking genipin derivative.Non-limiting examples of a bioerodible polymer are: a polyester, apolyester-containing copolymer, a polyanhydride, apolyanhydride-containing copolymer, a polyorthoester, and apolyorthoester-containing copolymer. In one embodiment, the polyester orpolyester-containing copolymer is a poly(lactic-co-glycolic) acid (PLGA)copolymer. In another embodiment, the bioerodible polymer is selectedfrom the group consisting of poly(lactic acid) (PLA); poly(trimethylenecarbonate) (PTMC); poly(caprolactone) (PCL); poly(glycolic acid) (PGA);poly(glycolide-co-trimethylenecarbonate) (PGTMC);poly(L-lactide-co-glycolide) (PLGA); polyethylene-glycol (PEG-)containing block copolymers; and polyphosphazenes. In one embodiment,the controlled release coating layer is a non-bioerodible polymercomprising the genipin or crosslinking genipin derivative.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 depicts one embodiment for use of genipin- or crosslinkinggenipin derivative-releasing coils for the improved treatment ofaneurysms.

FIG. 2. FIG. 2 illustrates a mechanism for genipin crosslinking ofproteins.

FIGS. 3A-3D depict non-limiting embodiments of a vaso-occlusive deviceas described herein.

DETAILED DESCRIPTION

The use of numerical values in the various ranges specified in thisapplication, unless expressly indicated otherwise, are stated asapproximations as though the minimum and maximum values within thestated ranges are both preceded by the word “about”. In this manner,slight variations above and below the stated ranges can be used toachieve substantially the same results as values within the ranges.Also, unless indicated otherwise, the disclosure of ranges is intendedas a continuous range including every value between the minimum andmaximum values. As used herein “a” and “an” refer to one or more.

Described herein are methods of treating aneurysms and devices useful intreating aneurysms. The methods employ a vaso-occlusive device that iscatheter-deployed, such as an embolism coil. The device comprises avaso-occlusive device that incorporates slow-releasing genipin, or acrosslinking genipin derivative, including pharmaceutically acceptablesalts thereof, as defined below and collectively referred to as “thecompound”. In further detail according to one embodiment, the deviceincludes a filamentous substrate, typically metallic, coated with apolymer that includes the genipin. The polymer can be bioerodible, andif not, the compound diffuses from the polymer at a controlled rate. Ifthe polymer is bioerodible, then the compound is released as the polymererodes, and the erosion rate is determined by the polymer compositionand can be tailored to erode over a time period extending from days toyears. A polymer coating that does not contain, or substantially oressentially does not contain (e.g., it is prepared without drug product,but may contain drug product leached from another layer), drug productcan be used to either coat the drug-containing layer, or be placed as anintermediary layer between the drug-containing layer and the underlying,typically metallic, substrate.

As used herein, the term “polymer” in general includes, for example andwithout limitation, homopolymer(s), copolymer(s), polymeric blend(s),block polymer(s), block copolymer(s), cross-linked polymer(s),non-cross-linked polymer(s), linear-, branched-, comb-, star-, and/ordendrite-shaped polymer(s), where polymer(s) can be formed into anyuseful form, for example and without limitation, a hydrogel, a porousmesh, a fiber, woven mesh, or non-woven mesh, such as, for example andwithout limitation, a non-woven mesh formed by electrospinning.

FIG. 1 provides a non-limiting embodiment of the disclosed methods anddevices. Currently available therapies include uncoated platinum coils,shown in the top panel. In that approach, (1) platinum coils areinserted into the fundus of the aneurysm (e.g., D 5 mm). (2) Thepresence of these coils induces clotting and eventual compaction to fillthe void. (3) However, over time the nascent clot can be cleaved byfibrolytic/thrombolytic enzymes, which ultimately leads to digestion anddestabilization of the clot. The ultimate mode of failure isrecanalization in which the occlusion is opened up again. The approachdescribed herein aims to use coils that release genipin or crosslinkingderivatives thereof. Genipin is a naturally-occurring compound that caninduce protein crosslinking via the formation of stable covalent bonds.Embolism coils are coated with a coating that can deliver genipin in acontrolled release manner. As shown in FIG. 1, bottom panel: (1) first,standard coil materials (i.e. platinum) are coated with a matrix ofpoly(L-lactide-co-glycolide) that is loaded with genipin; (2) theinsertion of these coils leads to rapid thrombus formation andsimultaneous release of genipin into the aneurysm, and (3) the bioactivegenipin then crosslinks the nascent clot with a unique covalentchemistry that is resistant to proteolysis. The crosslinked fibrin clotis then stabilized, which can reduce the risk of recanalization and isexpected to allow broader timelines for endothelialization, remodeling,and closure of the aneurysm.

In one embodiment, a bioactive coil is developed that can promoteaneurysm thrombosis and neoendothelial sealing of the aneurysm fundus.The novel method utilizes platinum coils that are coated with a polymermatrix that can control the local release of, for example, genipin, or aderivative thereof into the aneurysm. Genipin (Formula 1, methyl (1S,2R,6S)-2-hydroxy-9-(hydroxymethyl)-3-oxabicyclo[4.3.0]nona-4,8-diene-5-carboxylate,CAS No. 6902-77-8) is a naturally occurring compound that is found inthe fruit of the Gardenia jasminoides.

This bioactive compound can crosslink extracellular matrix moleculesthrough the formation of stable covalent crosslinks that are resistantto enzymatic degradation (Bigi, A., et al., Stabilization of gelatinfilms by crosslinking with genipin. Biomaterials, 2002. 23(24): p.4827-4832; Chang, Y., et al., Acellular bovine pericardia with distinctporous structures fixed with genipin as an extra cellular matrix. TissueEnginering, 2004. 10(5-6): p. 881-892; Liang, H.-C., et al., Effects ofcrosslinking degree of an acellular biological tissue on its tissueregeneration pattern. Biomaterials, 2004. 25(17): p. 3541-3552; Sung,H.-W., et al., Crosslinking of biological tissues using genipin and/orcarbodiimide. Journal of Biomedical Materials Research Part A, 2003.64A(3): p. 427-438; and Sung, H.-W., et al., Stability of a biologicaltissue fixed with a naturally occurring crosslinking agent (genipin).Journal of Biomedical Materials Research, 2001. 55(4): p. 538-546).Genipin stabilizes the formation of crosslinked gels based onbiopolymers that have amino acid residues with pendant primary aminessuch as aspargine (Asp, N), glutamine (Gln, Q), lysine (Lys, K), andarginine (Arg, R). This mechanism has been used to form mechanicallyrobust gels from gelatin and collagen (Bigi, A., et al., Stabilizationof gelatin films by crosslinking with genipin. Biomaterials, 2002.23(24): p. 4827-4832 and Sundararaghavan, H. G., et al., Genipin-inducedchanges in collagen gels: Correlation of mechanical properties tofluorescence. Journal of Biomedical Materials Research Part A, 2008.87A(2): p. 308-320). Genipin can crosslink fibrin (See, e.g., UnitedStates Patent Publication No. 2012/0189584).

Chemical crosslinks generated by the incorporation of genipin rendernetworks of extracellular matrices less susceptible to enzymaticdegradation. For example, genipin has been shown to limitinflammation-mediated degradation of agarose gels when used in tissueengineering applications (Lima, E. G., et al., Genipin enhances themechanical properties of tissue-engineered cartilage and protectsagainst inflammatory degradation when used as a medium supplement.Journal of Biomedical Materials Research Part A, 2009. 91A(3): p.692-700). In one example, genipin is used as a bioactive agent that canbe leveraged to form a stable thrombus within the fundus of theaneurysm. Increased stability of the thrombus reduces the risk ofenzyme-mediated recanalization, which is the primary mode of recurrence.

Genipin derivatives useful in the present invention include those withthe ability to react with primary amines and thereby cross-linkproteins, such as fibrin, comprising primary amines, which include aminoacid residues of asparagine (Asp, N), glutamine (Gln, Q), lysine (Lys,K) or Arginine (Arg, R). In the context of the present disclosure,useful genipin derivatives have the ability to crosslink fibrin and arereferred to herein as “crosslinking genipin derivatives”. Thedisclosures of U.S. Pat. Nos. 5,272,172, 6,162,826, 6,262,083, and7,649,014, each of which is incorporated herein by reference for thedisclosure of genipin derivatives many or most of which are expected toinclude protein crosslinking activity. A “genipin derivative” istherefore either a compound designated as such herein, an iridoidderivative as disclosed in U.S. Pat. No. 5,272,172, or a genipinderivative disclosed in any one of U.S. Pat. Nos. 6,162,826, 6,262,083,and 7,649,014, and includes stereoisomers and pharmaceuticallyacceptable salts thereof. Crosslinking activity for any given compoundis easily determined by a person of ordinary skill by mixing aprimary-amine-containing protein, such as fibrin with the candidatecompound and determining by any of a large number of available physical,chemical or optical assays whether or not the compounds arecross-linked. An Example of a useful crosslinking assay is described inU.S. Pat. No. 7,649,014 (column 38), where genipin forms a dark bluepigment when crosslinked by an amine nucleophile, such as: primaryamines such as methylamine; amino acids; and peptides.

U.S. Pat. No. 7,649,014 provides one criterion for distinguishingcross-linking genipin derivatives from non-crosslinking genipinderivatives. Without intent of being bound to this theory, incrosslinking genipin derivatives, primary amines replace the oxygen ofthe 3-oxane of genipin and its derivatives and the C8-C9 double bond andthe C9 primary alcohol appear to be required for crosslinking (See, FIG.2). To avoid confusion, numbering of the genipin structure, and genipinderivatives is in reference to the structure above, and not to thenumbering of any cited reference. Therefore, based on the disclosures ofU.S. Pat. Nos. 5,272,172, 6,162,826, 6,262,083, and 7,649,014, each ofwhich is incorporated herein by reference for the disclosure of genipinderivatives and methods of making genipin and genipin derivatives,exemplary crosslinking genipin derivatives include compounds of thefollowing formula 2, and stereoisomers and pharmaceutically acceptablesalts thereof:

In formula 2, R1 is —H, ═O or —OR4, where R4 is —H, C₁₋₆ alkyl, C₁₋₃alkyl, methyl, ethyl, propyl, isopropyl, butyl, n-butyl, t-butyl,isobutyl, sec-butyl, propylbenzyl, or C₁₋₁₂ alkanoyl which can besubstituted with phenyl, phenoxy, pyridyl or thienyl. R2 is H, C₁₋₆alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl, isopropyl, butyl, n-butyl,t-butyl, isobutyl, or sec-butyl. R3 is a primary alcohol chosen from—CH₂—OH and —R5-CH₂—OH, where —R5- is C₁₋₆ alkyl, C₁₋₃ alkyl, methyl,ethyl, propyl, isopropyl, butyl, n-butyl, t-butyl, isobutyl, orsec-butyl. As an example, for genipin: R1 is —OH, R2 is methyl, and R3is —CH₂—OH.

FIG. 2 illustrates a mechanism for Genipin Crosslinking of Proteins.Primary amines in virtually any protein (collagen, fibrin, gelatin,etc.) react with two genipin molecules to produce a covalent crosslink.The source of these amines arises from amino acid residues such asaspargine (Asp, N), glutamine (Gln, Q), lysine (Lys, K), and arginine(Arg, R). Two genipin molecules are consumed to form one covalentcrosslink between two residues. Furthermore, the molecular signature ofthis crosslink is widely resistant to degradation from fibrolytic andthrombolytic enzymes. This type of covalent crosslinking is well-suitedto stabilize nascent fibrin clots that are formed within intracranialaneurysms.

Butler et al. (“Mechanism and Kinetics of the Crosslinking Reactionbetween biopolymers Containing Primary Amine Groups and Genipin,” J.Polymer Science: Part A Polymer Chemistry (2003) 41:3941-3953) providesa different mechanism, including two alternate pathways, one implicatingthe ester group at the 5 position and the other, as an alternate to themechanism described above, involving C4, 03 and R1, wherein R1 is OH inone embodiment. Irrespective of the mechanism of crosslinking, thecompounds meeting the requirements of formula 2 are expected tocrosslink primary amine-containing compounds. The cross-linkingfunctionality of genipins are active with respect to a variety ofbiological macromolecules, such as fibrin and heparin, with excellentbiocompatibility. See, e.g., Tsai, C., et al., “Effects of HeparinImmobilization on the Surface Characteristics of a Biological TissueFixed with a Naturally Occurring Crosslinking Agent (Genipin): an InVitro Study,” (2001) Biomaterials 22:523-533).

As used herein, “genipin and crosslinking genipin derivatives” comprisepharmaceutically acceptable salts of genipin and the crosslinkinggenipin derivatives. A “pharmaceutically acceptable salt” as used hereinis intended to mean an active ingredient (drug) comprising a salt formof any compound as described herein. The salt form typically confers tothe improved and/or desirable pharmacokinetic/pharmodynamic propertiesof the compounds described herein, so long as crosslinking is notaffected. Pharmaceutically acceptable salts of any of the compoundsdescribed herein also may be used in the methods described herein.Pharmaceutically acceptable salt forms of the compounds described hereinmay be prepared by conventional methods known in the pharmaceuticalarts, and include as a class veterinarily acceptable salts. For exampleand without limitation, where a compound comprises a carboxylic acidgroup, a suitable salt thereof may be formed by reacting the compoundwith an appropriate base to provide the corresponding base additionsalt. Non-limiting examples include: alkali metal hydroxides, such aspotassium hydroxide, sodium hydroxide and lithium hydroxide; alkalineearth metal hydroxides, such as barium hydroxide and calcium hydroxide;alkali metal alkoxides, such as potassium ethanolate and sodiumpropanolate.

As used herein, a “vaso-occlusive device” refers, in one embodiment, toan elongate, flexible wire or filament prepared, for example and withoutlimitation from coiled metal, such as platinum or an alloy thereof,commonly used in the endovascular treatment of aneurysms, for exampleand without limitation by filling the dome or fundus of a saccularaneurysm. Such vaso-occlusive devices are often referred to as “embolismcoils.” Stents are often used for repair of fusiform aneurysms. Manyversions of this device are available commercially, and they includenon-coated (bare) metal devices and devices comprising coatings or othermodifications, such as inclusion of non-metal filaments. A commonembodiment of a vaso-occlusive device is known as a Guglielmi detachablecoil. As non-limiting examples of vaso-occlusive devices, U.S. Pat. Nos.7,896,899 and 8,273,100 depict bare metal devices as well as devicesincluding filaments incorporated within the metal structure and hydrogelcoatings. The filaments of the vaso-occlusive devices may be designatedas “framing” or “finishing” or “filling” in that some are used to createthe framework of the coiled mass within the aneurysm, while others are“softer” being more flexible and often including a hydrogel coating, andare used to fill the aneurysm. In one embodiment a “framing” coil isprepared from a shape memory alloy, such as nitinol, and optionally ispre-shaped prior to deployment, in the shape of a dome, sac or fundus ofa saccular aneurysm. A typical and non-limiting vaso-occlusive device isa flexible filament formed from a metal coil, braid, cut cylinder, etc.As is well-known in the art, a multitude of alternate configurations forthe vaso-occlusive device, or embolism coil are known, and aremodifiable according to the methods described herein. In the context ofthe methods and devices described herein, the configuration of theunderlying vaso-occlusive structure is not material so long as it can bemodified to release genipin and derivatives thereof useful in themethods. Although depicted as a filament, other shapes are capable ofdeployment by a catheter in endovascular methods, and any structureuseful for vascular occlusion can be used as a core structure that maybe modified to include elutable genipin or crosslinking genipinderivatives.

As would be recognized by those of ordinary skill, methods of treatingan aneurysm include not only use of a coated embolism coil, butconcurrent deployment of genipin or a crosslinking genipin derivative asdescribed herein with a standard embolic coil. The genipin orcrosslinking genipin derivative is preferably incorporated into acatheter-deployable slow-release dosage form, such as, withoutlimitation, a bioerodable polymer filament prepared from a bioerodiblepolymer according to any embodiment as described herein in the contextof the controlled release coating layer. The controlled release dosageform is deployed in the aneurysm fundus with, for example, an embolismcoil and stabilizes a clot formed within the aneurysm. For example, afiber is prepared from PLGA, containing an amount of genipin or acrosslinking genipin derivative effective to release in a 1 mL fundus or1 mL of an aqueous solvent of between 1 ng and 100 μg of the genipin ora crosslinking genipin derivative per day. The fiber is deployed into afundus of an aneurysm by a catheter before, during, or after deploymentof an embolism coil within the fundus. In one example, the fiber iswrapped about (around and/or intertwined with) an embolism coil.

Vaso-occlusive devices are typically deployed in an endovascularcatheter or microcatheter device as are broadly know in the arts fordeployment of such vaso-occlusive devices and stents. Common metals usedin the manufacture of such devices are biocompatible and preferablyradiodense (e.g., radiopaque), permitting visualization duringdeployment. Metals used in vaso-occlusive devices include: platinum,tantalum, iridium, tungsten, gold, titanium, and alloys thereof, such asnitinol and Elgiloy (Co—Cr—Ni). Alloys comprising a predominance ofplatinum, such as platinum-iridium or platinum-tungsten alloys arecommon.

FIG. 3A depicts schematically in cross section a simplified catheterstructure for deploying a vaso-occlusive filament. Catheter 10, ormicrocatheter, comprises a sheath 20 and a filament 30. FIG. 3A depictsonly a distal terminal end (away from a user of the device) of acatheter device, with the slash at left indicating that the catheterstructure continues. The proximal end of the catheter 10, including anycontrol structures for manipulation of the filament 30 or other featuresof the catheter that are not depicted for ease of understanding, is notshown. FIGS. 3B, 3C and 3D depict schematically variations in structureof the filament 30 depicted in FIG. 3A. Although FIGS. 3B-3D show ahelical coil structure, a very common structure to many embodiments ofthe filaments of vaso-occlusive devices, the helical coil structure is anon-limiting example provided for illustrative purposed only, and thefilament can have any structure, such as a braided structure or morecomplex configurations disclosed for example and without limitation inU.S. Pat. Nos. 7,896,899 and 8,273,100.

FIG. 3B shows schematically a bare metal filament 30, depicted forillustration purposes only as a helical metal coil. FIG. 3C showsschematically a filament 30 comprising a core 32, depicted forillustration purposes only as a helical metal coil, and a polymericcoating 34 comprising elutable genipin or a derivative thereof,indicated by speckling in the coating 34. FIG. 3D depicts schematicallyan alternate embodiment of the filament 30 depicted in FIG. 3A. Filament30 comprises a core 32, as in FIG. 3C, and a coating 34 comprisingelutable genipin or a crosslinking genipin derivative, and furthercomprises a polymeric intermediary layer 36 between the core 32 and thepolymeric coating 34. In one non-limiting embodiment, the coating 34comprises a bioerodible polymer, while intermediary layer 36 comprises apolymer, such as a swellable hydrogel as are known in the field ofvaso-occlusive devices. In one embodiment, the intermediary layer erodesmore slowly than the polymeric coating 34. Alternate materials can beused as an alternative to metals in the filament 30 of FIG. 3B and core32 of FIGS. 3C and 3D, such as biocompatible polymer structures havingthe desired flexibility. In many instances, however, metal is preferredfor use in the device for the core. For ease of description, the core 32is referred to as a “core substrate.”

In an alternate version of the device, and referring to FIG. 3D forcontext, the polymeric coating 34 does not contain drug, but can beerodable or non-erodable and the polymer is porous or non-porous. Theintermediary layer 36 is a polymeric substrate comprising the genipin orcrosslinking genipin derivative, and the polymeric coating controlsdiffusion of the drug from the intermediary layer and therefore from thedevice.

Vaso-occlusive devices are also broadly commercially available from manysources including: Codman & Shurtleff, Inc. of Raynham, Masachusetts(CASHMERE®, CERECYTE®, DELTAMAXX®, DELTAPAQ® and DELTAPLUS® microcoils);Covidien/ev3 Endovascular of Plymouth, Minn. (AXIUM™ detachable coilsystem); MicroVention, Inc. of Tustin, Calif. (MICROPLEX®, COSMOS®;HYPERSOFT® HYPERSOFT® 3D, and COMPASS® coils); Stryker Neurovascular ofFremont, Calif. (TARGET® and GDC 360° ® coils). Some of these devicesare “bare coil” devices as shown in FIG. 3B, while others, oftendesignated as “finishing coils” and the like, include a hydrogel as inFIG. 3C, but not including genipin or a derivative thereof. Thesecommercially-available devices can be modified by adding a controlledrelease genipin or genipin derivative element as described herein.

Genipin or a crosslinking genipin derivative (“the compound”) isincorporated into the structure of a vaso-occlusive device, such as afilament or an embolism coil so that the compound is released over anextended period of time that typically ranges from one day to severalmonths or longer, including increments therebetween. In one embodiment,the genipin is absorbed into, mixed with or attached to a coating on anembolism coil. In one embodiment, the compound is mixed with a polymericcoating material prior to application of the coating to a vaso-occlusivedevice, such as an embolism coil. In another embodiment, avaso-occlusive device, such as an embolism coil is first coated with apolymeric coating and the compound is applied to the polymeric coating,resulting in absorption of the compound into the polymeric coating oradsorption onto the polymeric coating. Incorporation of an active agent,such as genipin or a derivative thereof is referred to as “loading.” Inone embodiment, the polymeric coating may be applied to a surface of thecore substrate, for example by dipping or spraying (includingelectrospraying). The coating optionally is porous, as in a foam.

In another embodiment, the coating is applied as one or more fiberswound about (onto and/or into) the core substrate. Winding a fiber“within” the core substrate recognizes that many such core substratesare coils that include gaps between turns that exist in a relaxed stateof the coil, or when the coil is stretched, and the fibers can be woundbetween adjacent turns of the core substrate. The fibers can be loadedwith genipin or a derivative thereof prior to incorporation into thefilament structure, or the fibers can first be incorporated into thefilament structure and subsequently loaded. Filaments can be wound in aregular pattern about (around and/or within) a core substrate, orirregularly, as in a fiber mat, for example that is electrodepositedonto the core substrate.

As indicated above, genipin or a crosslinking genipin derivative iselutable from the vaso-occlusive device, meaning that the compound canfreely diffuse from the structure in an aqueous medium such as, withoutlimitation, water, saline, PBS (phosphate-buffered saline), blood orplasma such that the compound is released from the core substrate. Thecompound is not immediately releasable, meaning that the compound is notreleased as a single bolus upon exposure to blood. One reason for theundesirability of immediate release is to avoid release of the compoundinto the bloodstream, as genipin is known to have systemic effects. Anumber of mechanisms for slow or extended release of compounds areknown.

A first method of extending the release profile of the compound is toincorporate the compound in a slowly-dissolving biocompatible substanceon the core substrate, such that the compound is released into thebloodstream as the slowly-dissolving substance dissolves/erodes. In use,the compound is mixed into the slowly-dissolving substance and uponcontact with the blood in the aneurysm, the slowly-dissolving substancedissolves, releasing the compound. Carrier systems for slow release areknown in the compounding arts, and many are suitable for use inimplants. Exemplary compositions typically include excipients such as,without limitation: magnesium stearate, a polyethylene glycol (PEG),glycerol, cellulose or cellulose derivatives, such as microcrystallinecellulose or carboxymethylcellulose, a non-ionic detergent such asTWEEN®, and sugars, such as lactose, and mixtures thereof. Suitablecandidates for slowly-dissolving substance include small molecules witha molecular weight below 2000 g/mol. These are incorporated into or ontothe device by any suitable process, such as by drying a slurry or meltof the mixture onto the device.

A second method for the slow deployment of the genipin or crosslinkinggenipin derivatives is to absorb or adsorb the compound into and/or ontoa coating of the device. The coating can be a microporous or non-porousstructure, optionally including a drug-free top coat, prepared, forexample, from a polymer, such as, without limitation, silicone orpolysiloxanes, polyurethane, poly(ether urethane) urea, polyacrylates orPTFE (polytetra-fluoroethylene). In one non-limiting example, thecomposition is a blend (e.g., 67% to 33%) of poly(ethylene-co-vinylacetate) and poly(n-butyl methacrylate) (PEVA-PBMA). A drug-free toplayer or top coat of PBMA, or any suitable polymer also can be added tofunction as a barrier through which drug elutes out under diffusion,thereby further controlling the rate of release. In another non-limitingembodiment, poly(styrene-b-isobutylene-b-styrene), or SIBS, ahydrophobic triblock copolymer composed of styrene and isobutylene unitsbuilt on 1,3-di(2-methoxy-2-propyl)-5-tert-butylbenzene, may be used toprovide controlled, slow release of the compound. In yet anotherembodiment, vinylidene fluoride and hexafluoropropylene (PVDF-HFP)copolymer—an acrylic and fluoro copolymer made from vinylidene fluoride(VF) and hexafluoropropylene (HFP) monomers—is used to providecontrolled release of the compound. Although the composition can beerodible in vivo, the mechanism of drug release is by diffusion.

A third method for slow deployment of the genipin or crosslinkinggenipin derivatives is to incorporate the compound into a biocompatible,bioerodible matrix. This is typically achieved by mixing the compoundwith a polymer solution prior to incorporation of the polymer solutioninto the vaso-occlusive device, or forming any other useful structurefor delivery of the compound to the aneurysm fundus. The compound iseluted from the polymeric matrix by bioerosion and to some extentdiffusion from the surface or from near the surface of the polymer. By“bioerodible,” it is meant that a polymer, once implanted and placed incontact with bodily fluids and/or tissues, will degrade either partiallyor completely through chemical, biochemical and/or enzymatic processes.Non-limiting examples of such chemical reactions include acid/basereactions, hydrolysis reactions, and enzymatic cleavage. In certainnon-limiting embodiments, the biodegradable polymers may comprisehomopolymers, copolymers, and/or polymeric blends comprising, withoutlimitation, one or more of the following monomers: glycolide, lactide,caprolactone, dioxanone, and trimethylene carbonate. In othernon-limiting embodiments, the polymer(s) comprise labile chemicalmoieties, non-limiting examples of which include esters, anhydrides, orpolyanhydrides, which can be useful in, for example and withoutlimitation, controlling the degradation rate of the scaffold and/or therelease rate of therapeutic agents from the scaffold.

The polymeric components used to make the bioerodible coating(s) arepreferably biocompatible. By “biocompatible,” it is meant that a polymercompositions and its normal degradation in vivo products arecytocompatible and are substantially non-toxic and non-carcinogenic in apatient within useful, practical and/or acceptable tolerances. By“cytocompatible,” it is meant that the polymer can sustain a populationof cells and/or the polymer composition, device, and degradationproducts thereof are not cytotoxic and/or carcinogenic within useful,practical and/or acceptable tolerances. For example, the polymer whenplaced in a human epithelial cell culture does not adversely affect theviability, growth, adhesion, and number of cells. In one non-limitingembodiment, the compositions and/or devices are “biocompatible” to theextent they are acceptable for use in a human or veterinary patientaccording to applicable regulatory standards in a given jurisdiction. Inanother example the biocompatible polymer, when implanted in a patient,does not cause a substantial adverse reaction or substantial harm tocells and tissues in the body, for instance, the polymer composition ordevice does not cause necrosis or an infection resulting in harm totissues from the implanted scaffold.

Useful bioerodible polymeric compounds are known in the medical andpharmaceutical arts. Bioerodible polymers are polymers that are brokendown over a desired time period. Among other factors, the composition ofa polymer and the three-dimensional structure thereof will dictate thespeed of erosion when implanted. Typical erosion times range from 24hours up to two years and increments there between. In the context ofthe present disclosure, the erosion time for the coating containing thecompound is from one week to two years, for example from two to sixmonths. The polymer and the dissolution products thereof arebiocompatible in that they do not cause or elicit unsafe or toxiceffects when implanted. Suitable polymers are known in the medical arts,with polyesters being common in such applications. Polyesters includehomopolymers and copolymers, including block copolymers, such as,without limitation: poly(lactic acid) (PLLA); poly(trimethylenecarbonate) (PTMC); poly(caprolactone) (PCL); poly(glycolic acid) (PGA);poly(glycolide-co-trimethylenecarbonate) (PGTMC);poly(L-lactide-co-glycolide) (PLGA); polyethylene-glycol- (PEG-)containing block copolymers, such as PEG-PLGA-PEG or PEG-PLA-PEG blockcopolymers; and polyphosphazenes, such as polyorganophosphazenes.Non-erodable polymers either do not erode substantially in vivo or erodeover a time period of greater than two years. Compositions such as, forexample and without limitation, PTFE, poly(ethylene-co-vinyl acetate),poly(n-butylmethacrylate), poly(styrene-b-isobutylene-b-styrene) andpolyethylene terephthalate are considered to be non-erodable polymers.Other suitable non-erodable polymer compositions are broadly known inthe art, for example in stent coating and transdermal reservoirtechnologies.

The bioerosion profiles of copolymers and block copolymers can bealtered by changing the relative ratio of monomers in the copolymer. Forexample and without limitation, the ratio of lactic acid to glycolicacid monomers incorporated into a PLGA composition with alter thebioerosion speed of the copolymer. As a consequence, useful PLGAcomposition comprise, in terms of molar quantities or number, from 1% to99% lactic acid residues and from 99% to 1% glycolic acid residues(incorporated monomers of lactic acid or glycolic acid in the polymer),or molar feed ratios of 1% to 99% lactic acid and from 99% to 1%glycolic acid in the polymerization mixture, resulting in a similarmolar ratio in the final product of respective residues. Otherco-polymers, such as polyorganophosphazenes can be tailored forbioerosion duration accordingly.

Additional active agents may be incorporated into the device for releaseby any suitable method, such as those methods described above. Thesemany include therapeutics such as, without limitation:antihypertensives, such as calcium channel blockers, for example andwithout limitation the dihydropyridines nimodipine and nifedipine, andbeta blockers, such as propranolol. In another embodiment, a secondsmall molecule crosslinking agent in addition to genipin or crosslinkingderivatives thereof, such as glutaraldehyde, is incorporated into thedevice in non-toxic quantities, and is administered by the deviceaccording to the methods described herein.

It will be recognized that various combinations or layers ofdrug-containing and drug-free polymers may be combined to alter therelease profile of the composition. For example a bioerodible layer maybe placed above a non-erodible layer (See, e.g., FIG. 3D) such that drugis released over time, but a polymeric coating remains on the filament.Likewise a drug-free layer can overlay a drug-containing layer toregulate release of the drug by dissolution, determined, for example, bythe thickness, permeability and porosity of the drug-free layer.

The polymer for the previous two embodiments in which the genipin isreleased by diffusion and/or erosion of a substrate may or may notcomprise primary amines. If the polymer comprises primary amines, thegenipin or crosslinking genipin derivative will crosslink the polymer,and the amount of compound used in the crosslinking would need to beaccounted for in the product design. If primary amines are present inthe polymer, then effective amounts of the genipin or crosslinkinggenipin derivative would need to be added above the amount of genipinincorporated into the polymeric structure via primary amines.

The field of coating stents and release of drugs from stents iswell-developed, and the methods for delivering an active agent from thestructure described herein in the context of occlusion of aneurysms bydissolution of a carrier substrate, by diffusion from a polymericmaterial or by bioerosion of a polymeric material, can be extended tothe devices and methods described herein.

In an alternate embodiment, the compound can be introduced into the samelocation as the vaso-occlusive device during deployment of the device,but separately from the device. A slow-release drug product, in the formof a fiber or other structure, can be deployed into the desired locationsuch as the sac of the aneurysm. The three-dimensional shape of the drugproduct is less material to the operability of this embodiment so longas the product can be deployed from a catheter into an aneurysm and canrelease the compound according to a useful profile. As a non-limitingexample, a polymeric fiber prepared from a bioerodible, biocompatible(co)polymer (for example and without limitation, a polyester such asPLA, PGA or PLGA and other compositions described above and/or as arebroadly known) and containing therein a safe and effective amount of thecompound, can readily be deployed within an aneurysm.

In one embodiment, the treatment method is as follows. (1) First,standard coil materials (e.g., platinum or an alloy thereof) are coatedwith a matrix of poly(L-lactide-co-glycolide) that is loaded withgenipin. (2) The insertion of these coils leads to rapid thrombusformation and simultaneous release of genipin into the aneurysm. (3) Thebioactive genipin then crosslinks the nascent clot with a uniquecovalent chemistry that is resistant to proteolysis. The crosslinkedfibrin clot is then stabilized which can reduce the risk ofrecanalization and will allow broader timelines for endothelialization,remodeling, and closure of the aneurysm.

In one embodiment, a method is used whereby controlled release strategyis integrated with platinum coils for delivering bioactive agents intothe fundus of the aneurysm. Furthermore, an inert matrix based on PLGAmethod is used because PLGA is a material that is generally recognizedas safe (e.g., GRAS material). Furthermore, there have been severalpre-clinical and clinical trials that have deployed PLGA-based devicesfor use in treating intracranial aneurysms. PLGA is also a suitablematrix for the controlled release of small molecules including genipin.Genipin and PLGA share many common organic solvents and are compatiblewith many coating techniques that are based on solution-processingincluding acetone and dichloromethane. Sustained release of genipin intothe nascent fibrin clots within the fundus may create a stable clot thatis resistant to enzymatic degradation, remodeling, and recurrence viarecanalization.

By the methods described herein, an organized thrombus is stabilized andremains localized within the coil interstices, the presence of thisorganized scar across the neck can produce a suitable matrix for cellmigration. Specifically, the genipin-crosslinked proteins serve as ascaffold to enable efficient migration of neointimal cells from thesurrounding vessels, which can grow and advance to cover and seal theaneurysm neck. In one example, genipin is safe for use in treatingintracranial aneurysms given the extensive history of use as a bioactivecompounds in other applications. While cytotoxicity studies have shownthat this substance can cause cell death to L929 fibroblasts, theseadverse effects are limited to exposures of 5 mM and 10 mM. Forcross-linking purposes, cell samples incubated in 1 mM wereindistinguishable from controls (Sundararaghavan, H. G., et al.,Genipin-induced changes in collagen gels: Correlation of mechanicalproperties to fluorescence. Journal of Biomedical Materials ResearchPart A, 2008. 87A(2): p. 308-320.

As a consequence, the devices and methods described herein release asafe and effective amount of genipin or a crosslinking genipinderivative. By safe, it is meant a non-toxic amount of the compound,releasing the compound at a rate not to exceed an amount of genipin inthe aneurysm fundus (typically less than 1 mL in volume) to exceed 5 mM(millimolar) and preferably less than 5, 4, 3, 2, 1, 0.5 or 0.1 mM. Itshould be noted that the packing of an aneurysm fundus requires variableamounts of vaso-occlusive filament. As such, the amount of the compoundreleased per designated time period per unit length of the filament ismost relevant. Elution profiles for any given filament can readily bedetermined empirically by submerging a fixed length of the filament inPBS or plasma and determining by e.g., spectroscopy, the amount of thecompound released over time. For example, and without limitation, thefilament or filaments release no more than from 1 ng to 100μg of thegenipin or crosslinking genipin derivative into the aneurysm sac perday. For example, in use, and/or when placed in an aqueous solvent, suchas water, PBS, saline, or plasma, a 10 cm length of a filament asdescribed in any embodiment presented herein releases between 1 ng and100 μg of genipin per day. It should be noted that the genipin-releasingor crosslinking genipin derivative-releasing filaments described hereincan be deployed in fixed lengths into an aneurysm fundus, and additionalfilaments that do not release the compound can be used to fill theaneurysm. This method may be used to control the amount of the compoundreleased into the fundus.

Example

Safety and efficacy of the vaso-occlusive devices are tested as follows.Embolism coils are prepared by coating platinum, platinum alloy ornitinol embolism coil, optionally pre-coated with a hydrogel, with alayer of PLGA (25%, 50% and 75% lactic acid, molar feed ratio). The PLGAis mixed with 0.0, 0.01, 0.1, 0.25, 0.5, 1.0, 5.0 and 10.0 mg/mL genipinor a crosslinking genipin derivative. The coils are dried, sterilizedand stored at room temperature. One or more of the coils, and controlcoils (no hydrogel and/or 0.0 mg/mL of active compound), are tested in arabbit model, essentially as shown in Reinges, M. H. T, et al.,Ineterventional Neuroradiology (2010) 16:139-150.

The present invention has been described in accordance with severalexamples, which are intended to be illustrative in all aspects ratherthan restrictive. Thus, the present invention is capable of manyvariations in detailed implementation, which may be derived from thedescription contained herein by a person of ordinary skill in the art.

1. A method of treating an aneurysm in a patient, comprising feeding avaso-occlusive device and genipin or a crosslinking genipin derivativeinto a fundus of the aneurysm using a catheter.
 2. The method of claim1, in which the genipin or a crosslinking genipin derivative isincorporated into a bioerodible polymer.
 3. The method of claim 1, inwhich the genipin or a crosslinking genipin derivative is incorporatedinto a non-bioerodible polymer.
 4. The method of claim 1, in which thevaso-occlusive device comprises a core substrate and a controlledrelease coating layer on the core substrate comprising the genipin or acrosslinking genipin derivative.
 5. The method of claim 4, in which thecontrolled release coating layer comprises genipin or a pharmaceuticallyacceptable salt thereof.
 6. The method of claim 4, in which thecontrolled release coating layer comprises a crosslinking derivative ofgenipin or a pharmaceutically acceptable salt thereof.
 7. The method ofclaim 4, in which the crosslinking derivative of genipin is a compoundaccording to formula 2, or a stereoisomer or pharmaceutically acceptablesalt thereof:

where R1 is —H, ═O or —OR4, where R4 is —H, C₁₋₆ alkyl, C₁₋₃ alkyl, orC₁₋₁₂ alkanoyl which can be substituted with phenyl, phenoxy, pyridyl orthienyl; R2 is H, C₁₋₆ alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl,isopropyl, butyl, n-butyl, t-butyl, isobutyl, or sec-butyl; and R3 is aprimary alcohol chosen from —CH₂—OH and —R5-CH₂—OH, where —R5- is C₁₋₆alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl, isopropyl, butyl, n-butyl,t-butyl, isobutyl, or sec-butyl, other than genipin.
 8. The method ofclaim 7, in which R1 is —OR4, where R4 is —H or C₁₋₃ alkyl.
 9. Themethod of claim 8, in which R2 is H or C₁₋₃ alkyl and/or R3 is —CH₂—OH,—CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH.
 10. The method of claim 7, in which R2is H or C₁₋₃ alkyl.
 11. The method of claim 7, in which R3 is —CH₂—OH,—CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH.
 12. The method of claim 4, in which thedevice comprises between the core substrate and the controlled releasecoating layer a polymeric intermediary layer.
 13. The method of claim12, in which the polymeric intermediary layer is a hydrogel.
 14. Themethod of claim 4, in which the controlled release coating layer is abioerodible polymer comprising the genipin or crosslinking genipinderivative.
 15. The method of claim 14, in which the bioerodible polymeris a polyester or a polyester-containing copolymer.
 16. The method ofclaim 15, in which the polyester or polyester-containing copolymer is apoly(lactic-co-glycolic) acid (PLGA) copolymer.
 17. The method of claim14, in which the bioerodible polymer is selected from the groupconsisting of a polyanhydride, a polyanhydride-containing copolymer, apolyorthoester, and a polyorthoester-containing copolymer.
 18. Themethod of claim 14, in which the bioerodible polymer is selected fromthe group consisting of poly(lactic acid) (PLA); poly(trimethylenecarbonate) (PTMC); poly(caprolactone) (PCL); poly(glycolic acid) (PGA);poly(glycolide-co-trimethylenecarbonate) (PGTMC);poly(L-lactide-co-glycolide) (PLGA); polyethylene-glycol- (PEG-)containing block copolymers; and polyphosphazenes.
 19. The method ofclaim 4, in which the controlled release coating layer is anon-bioerodible polymer comprising the genipin or crosslinking genipinderivative.
 20. A vaso-occluding catheter device comprising a sheath anda filament within the sheet, the filament comprising a core substrateand a controlled release coating layer on the core substrate comprisinggenipin or a crosslinking genipin derivative.
 21. The device of claim20, in which the core substrate is a metal.
 22. The device of claim 21,in which the metal is platinum, a platinum alloy or nitinol.
 23. Thedevice of claim 20, in which the controlled release coating layercomprises genipin or a pharmaceutically acceptable salt thereof.
 24. Thedevice of claim 20, in which the controlled release coating layercomprises a crosslinking derivative of genipin or a pharmaceuticallyacceptable salt thereof.
 25. The device of claim 24, in which thecrosslinking derivative of genipin is a compound according to formula 2,or a stereoisomer or a pharmaceutically acceptable salt thereof:

where R1 is —H, ═O or —OR4, where R4 is —H, C₁₋₆ alkyl, C₁₋₃ alkyl, orC₁₋₁₂ alkanoyl which can be substituted with phenyl, phenoxy, pyridyl orthienyl; R2 is H, C₁₋₆ alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl,isopropyl, butyl, n-butyl, t-butyl, isobutyl, or sec-butyl; and R3 is aprimary alcohol chosen from —CH₂—OH and —R5-CH₂—OH, where —R5- is C₁₋₆alkyl, C₁₋₃ alkyl, methyl, ethyl, propyl, isopropyl, butyl, n-butyl,t-butyl, isobutyl, or sec-butyl, other than genipin.
 26. The device ofclaim 25, in which R1 is —OR4, where R4 is —H or C₁₋₃ alkyl.
 27. Thedevice of claim 26, in which R2 is H or C₁₋₃ alkyl and/or R3 is —CH₂—OH,—CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH.
 28. The device of claim 25, in which R2is H or C₁₋₃ alkyl.
 29. The device of claim 25, in which R3 is —CH₂—OH,—CH₂—CH₂—OH, or —CH₂—CH₂—CH₂—OH.
 30. The device of claim 20, in whichthe device comprises between the core substrate and the controlledrelease coating layer a polymeric intermediary layer.
 31. The device ofclaim 30, in which the polymeric intermediary layer is a hydrogel. 32.The device of claim 20, in which the controlled release coating layer isa bioerodible polymer comprising the genipin or crosslinking genipinderivative.
 33. The device of claim 32, in which the bioerodible polymeris a polyester or a polyester-containing copolymer.
 34. The device ofclaim 33, in which the polyester or polyester-containing copolymer is apoly(lactic-co-glycolic) acid (PLGA) copolymer.
 35. The device of claim32, in which the bioerodible polymer is selected from the groupconsisting of a polyanhydride, a polyanhydride-containing copolymer, apolyorthoester, and a polyorthoester-containing copolymer.
 36. Thedevice of claim 32, in which the bioerodible polymer is selected fromthe group consisting of poly(lactic acid) (PLLA); poly(trimethylenecarbonate) (PTMC); poly(caprolactone) (PCL); poly(glycolic acid) (PGA);poly(glycolide-co-trimethylenecarbonate) (PGTMC);poly(L-lactide-co-glycolide) (PLGA); polyethylene-glycol- (PEG-)containing block copolymers; and polyphosphazenes.
 37. The device ofclaim 20, in which the controlled release coating layer is anon-bioerodible polymer comprising the genipin or crosslinking genipinderivative.